DETERMINING STANDARD OPERATIONAL VALUE FOR DELAY TIME OF
A RADIOGRAPHIC SYSTEM
Field of the invention
The present invention relates to a method for the determination and use of a
standard operational value for the delay time of a radiographic system used
in medical radiographic applications. More in particular the method relates
to a technique to determine the delay time or start-time of a generator, used
in combination with a digital radiographic detector, a so-called FPD, Flat
Panel Detector, and to use same as standard operational value for
radiographic exposures.
Background of the invention :
It is known that radiographic illumination has important applications in
medical imaging, whereby the medical advantages for the patient largely
exceed the small risk of damage resulting from such radiographic
illumination. The formation of images is a result of the fact that radiographic
illumination, depending on the energy, passes through most soft tissues, but
does not pass the harder calcium-containing tissue. So, as an example, bones
will bar most radiographic illumination whereas cartilage will bar such
illumination to a much lesser extent. As a result, since more than a century,
the human skeleton can easily be visualised by radiographic illumination.
Radiographic illumination is also applied in medicine in radio therapeutic
applications. For the application of the present invention however
radiographic illumination is used for medical imaging applications, more in
particular for medical diagnosis.
Radiographic illumination generally is generated in an X-ray tube as
'Bremsstrahlung'. An example of such an x-ray tube is shown in figure 2.
This radiation is generated when accelerated electrons impinge on a target,
mostly made of tungsten of another hard material such as molybdenum with
a melting point above 2 000 degrees Celsius. The electrons are accelerated
under vacuum (10-5 Pascal) by use of an electric current. A tension
difference (anode tension) generates such field between the cathode K and
the anode A. Electrons are liberated from the Cathode K by heating same, for
example by means of a resistance wire of filament, whereupon an
incandescent tension is applied, causing an incandescent current that
generates a local heating.
At around 2 700 K electrons are generated around the tungsten filament that
can escape from such material at these elevated temperatures. As such
electrons are negatively charged, they are accelerated by a strong electric
field (30 - 150 kV depending on the application) over a distance of a few
millimetre from the negative cathode to the positive anode. The maximal
energy of the radiographic illumination generated in this way is proportional
to the electrical voltage applied; therefore is usually is expressed as kiloelectron
volt. The intensity is depending on the electrical current that is
generated. This is expressed in mA (mill amperes).
When generating such intense radiographic illumination, the target, the
anode, is heated intensively. As a result, radiographic tubes are provided with
cooling arrangements (for example water cooling and/or are characterised by
a high rotational speed of the target (rotating-anode).
The anode mostly is made of metal. In the anode material the electrons are
intensively slowed down, producing a radiographic illumination having an
energy comprised between O and the total voltage of the electric field. This
illumination is called Bremsstrahlung. On top hereof a high number of such
electrons will be slowed down by collision with electrons in the anode
material and will ionise atoms by liberating electrons from the inner shells.
When such electrons fall back to such inner shells, so-called characteristic
radiation is generated, depending on the kind of metal the anode is made of.
In case of a cupper-anode this radiation is around 8 keV, whereas in case of
molybdenum this radiation amounts to approx. 18 keV. The total charge of a
radiation tube is a few kilowatts, the surface whereupon the electrons
impinge is between 0.5 and 10 square millimetre.
For use in medical imaging applications, two kinds of radiation tubes are
used, differing as regards the construction of the anode. All tubes consist of a
glass tube wherein the all components are present under high vacuum. One
type of radiation tube comprises a fixed anode, whereas the other comprises a
rotating anode. Because all tubes and casings are fully closed, it is not
possible to use a cooling medium from outside, as was the case in the past.
The only possibility is the discharging of the energy generated by radiation.
To this end, the tube is surrounded by an amount of air-free high-quality oil.
A switch is foreseen that will automatically interrupt the current in case of
expansion of the oil by heating; in this way the tube is protected against
overheating.
This is the original model, whereby the anode usually is made of cupper,
characterised by an excellent heat conductivity.
This model is mostly used in apparatuses with a limited power as used for
example in dentist applications, in portable and mobile units.
To achieve an improved discharge of the heat, the rotating anode concept has
been developed. In this concept, use is made of a massive disc of tungsten or
an alloy of tungsten and rhenium. The place where the electrons impinge is
not limited to approximately 1 square centimetre, but consists of a circle over
the disc surface, the so-called line focus. Also a second incandescent
filament can be mounted in the cathode, that focuses on a smaller of larger
surface on the anode. A small target surface (focus) is characterised by less
scattering and thus less geometrical unsharpness. For small objects (hands,
feet, small joints) one usually chooses the smallest possible focus for a
maximal rendering of details.
The anode is formed by the disc, the support and the anode body that
functions as the rotor of an electromotor. At the outside magnets are
mounted (stator) that enable the anode to quickly turn around. Depending
on the tube-type the rotating velocity is situated between 4000 and 9000
revolutions per minute. The angle of the anode is usually situated between
10° and 20°, which is much smaller than in case a fixed anode is used. Tubes
having a rotating anode usually have much more components that fixedanode
tubes and the steering thereof requires much more electronic circuitry.
Consequently these models are much more expensive compared to the more
simple models. The efficiency of tubes with a rotating anode is however
much higher and the application of this type of tubes practically has no
limits.
The invention as described hereinafter relates to radiation tubes with a
rotating anode; these types of tubes are most common nowadays, in
particular for general purpose radiography (genrad), as well as for
mammographic applications (mammo).
As is known to those skilled in the art, in case of a radiographic illumination
with a D Panel, the generator should first receive a signal that the anode
should be brought to speed, and the filament or incandescent wire of the
cathode should be heated to a red/white state.
After a certain amount of time which is required for the above - this is the socalled
generator delay time or start-up time - the expose or illumination
button can be activated, whereby the generator is brought under high
tension.
In case the operator activates both buttons simultaneously, or in case of a
combined prep-expose button, activates the button at full, a pre-determined
fixed delay time will cause the high tension to occur only after the anode is
brought to speed and the filament or incandescent wire is heated to the
red/white state.
This start-up or delay time of the radiographic generator should be known.
These times differ for the various types of radiographic generators that are on
the market.
This problem in particular arises when an existing radiographic exposure
unit in a hospital was used in combination with radiographic detectors such
as film or stimulable phosphors, and now should be used in combination with
fully digital radiographic detectors, such as flat panel detectors.
This is the so-called retrofit situation, known to the person skilled in the art of
medical radiography.
One of the crucial differences between the use of radiographic films or
stimulable phosphors, as contrary to fully digitized panels, is that films and
stimulable phosphors are always 'ready' to be exposed.
The only limitation for a film is that it should not be exposed and/or
developed in an earlier stage, and in case of a stimulable phosphor screen,
that it has been erased after a prior exposure.
Provided these conditions are met, both radiographic media are always apt to
be used in a radiographic exposure.
The radiographic workflow in case a fully digitized radiographic panel is
used, on the contrary, is rather different. The reason for this is that in most
cases a radiographic digital panel should first be reset. This resetting is
known to the person skilled in the art, and is described amongst others in the
Handbook of Medical Imaging, Vol. 1, Chapter 4 : Flat Panel Imagers for
digital radiography, (ed. R.V. Matter et al., SPIE Press, Bellingham, 2000.)
The resetting of a radiographic digital panel, and the problems caused hereby
in case of a change-over of an existing radiographic exposure unit, previously
used in combination with film or stimulable phosphor plates, to a unit based
on the use of digital radiographic detectors, is published in a great number of
earlier patent specifications, amongst others in EP 2 209 422.
The global aim in case of a radiographic exposure is that the integration time
of the panel or the digital radiographic detector overlaps with the exposuretime
of the generator. More in particular, the integration time should
somewhat exceed the exposure time to be sure no radiographic diagnostic
information is lost.
To this end it is essential to know the applicable generator delay time.
Indeed, suppose the start-up of the generator would coincide with the
integration time of the direct radiographic panel, then it is not excluded that
the integration time has expired at the moment the effective exposure starts.
Such a procedure evidently would not lead to an image useful for medical
diagnosis.
In practice, a radiographic exposure can take place according to two different
ways. First the radiographic operator activates the prep button of the
apparatus, e.g. on the retrofit box.
The patient to be radiographed is then requested to keep still and not to
breathe temporarily (in case of a chest exposure). As set forth supra, the
generator then receives a signal to bring the anode to speed and to heat the
filament.
In case the operator waits sufficiently long for the activation of the expose
button, until the generator's rotating anode is effectively up to speed (the socalled
generator delay time), no problem arises.
When the exposure button is activated by the operator, a signal is sent to the
DR panel to reset same, and once this is done, over the retrofit box a signal is
sent to the generator to start the exposure.
The generator is ready to perform same because its generator delay time has
expired, in other words, because the generator has had enough time to
prepare the exposure.
Problem :
The problem arises when - as is often the case in practical circumstances -
the operator activates, e.g. by pressing, the prep and exposure buttons
simultaneously, or in case the operator pushes through (in case the prep and
exposure buttons are integrated in one and the same button or device, that
can be activated as well in part as in full).
In such a case, the problem can arise that the generator receives an expose
signal at a time the generator is not ready for this, in other words, because its
anode is not yet brought to speed, and/or the filament wire is not sufficiently
heated.
In such embodiment, the generator will necessarily wait to commence the
exposure until the time the rotating anode is up to speed, but in the
meantime the panel is ready to receive the radiographic illumination,
differently phrased, the panel is integrating same, but there does not exist a
meaningful radiographic signal to integrate. In the worst case scenario, the
generator starts to perform exposure at a time the panel again is closed,
because for example its integration time has expired.
In such scenario the above situation often leads to a so-called retake, which
means that the patient will be exposed again. This evidently should be
avoided, given the inherent harmful effect of any radiographic exposure on
the health condition of patients.
The objective of the present invention is to overcome the abovementioned
problems and disadvantages.
Summary of the invention
The present invention relates to a method for the determination of the delay
time of a radiographic generator used in medical radiographic systems, and
the use hereof as standard operational value for the delay time of the
corresponding radiographic system, comprising the following steps :
• selection of a sufficiently high delay-time for the radiographic
generator on a retrofit box;
• Simultaneous transmission of the preparation- and exposure signal
from the retrofit box to the generator console;
• Determining whether at the expiration of the selected delay time a
confirmation signal for the start of the radiographic exposure has been
submitted by the radiographic generator;
• In case such a confirmation signal has been submitted, repeating the
abovementioned three steps, whereby the delay-time is reduced by a
factor two;
• In case no such confirmation signal has been submitted, repeating
once the abovementioned three steps, whereby a value is selected for
the delay time mid-way the value whereby a confirmation signal still
has been obtained, and the value whereby such signal has not been
obtained any more;
• The last value of the selected delay-time whereby a confirmation
signal still has been given by the radiographic generator, is retained as
standard operational value for the delay time of the radiographic
system by the retrofit box.
According to a preferred embodiment of the invention, the method
comprises a step whereby the initially selected sufficiently high delay time
amounts to at least 10 seconds.
According to a further preferred embodiment the method comprises a step
whereby the preparation and exposure signals are submitted simultaneously
by simultaneous activation of the preparation and exposure buttons on a
retrofit box.
The present invention also relates to a method for taking a radiographic
exposure, whereby the radiographic image is captured by a radiographic
digital detector and, in case the radiographic operator generates an exposure
signal to the retrofit box at a time that the delay time of the generator,
counted as from the submission of the preparation signal by the operator, has
not expired yet, that the retrofit box transmits this exposure signal to the
radiographic generator after expiration of the standard operational delay
time as determined by the method as described above, and more in particular
in claims 1 through 3, and counted as from the transmission of the
preparation signal from the retrofit box to the radiographic generator.
According to a preferred embodiment of the above method, the retrofit box
will transmit the exposure signal to the radiographic generator, after a
positive reset signal has been received by the digital radiographic detector.
The invention also relates to a radiographic recording system, comprising a
radiographic generator, a console and an exposure unit, a digital radiographic
detector, a retrofit box and means for detecting by the retrofit box of a
preparation signal and an exposure signal, characterised in that the retrofit
box uses a standard operational value for the delay time for the transmission
of the exposure signal to the generator, whereby said standard operational
value is determined by means of the method described as set forth above, and
more in particular as set forth in any of claims 1 through 3.
According to a preferred embodiment of the said system, the means for
detecting the preparation signal and the exposure signal comprise a two-stage
push button operationally coupled to the retrofit box.
Description of the invention
Short description of the drawings
Figure 1 shows a schematic bloc diagram of a radiographic configuration for
the implementation of the method according to the invention.
Figure 2 shows a drawing in principle of a radiographic generator whereupon
the method of the present invention can be applied.
According to the schematic block diagram of Figure 1, the Generator
Console shows a console from where the radiographic generator, shown by
the bloc marked 'generator' can be steered. On its turn the generator takes
care that the radiographic tube, marked by the bloc 'tube', emits radiographic
emission, shown by the dashed arrow, that is captured by a radiographic
digital detector. The digital radiographic detector is shown by the bloc
marked 'DR Panel'.
This DR panel on its turn is connected to the workstation, shown by the bloc
'NX Workstation'. This workstation may comprise a display means with
related CPU, whereupon the radiographic image can be visualised for
observation by a radiologist for determination of a clinical diagnosis.
The DR Panel is in operational communication with a central steering unit,
called retrofit-box. The operation of such box is described hereinafter.
This unit also comprises a module that allows the operator to perform the
necessary instructions to the radiographic unit, such instructions comprising
a so-called prep and expose-signal.
These instructions can be transmitted to the retrofit box in a variety of
manners.
A first embodiment comprises a retrofit box having two separate pushbuttons,
one for the transmission of the prep signal, and a second one for the
transmission of the expose signal. These commands may be integrated in
one and the same push-button, that either can be pushed mid-way or at full
for transmitting either the prep, or the expose command.
An alternative embodiment is that these commands can be transmitted by
means of a computing device, provided with either a keyboard or a touch
screen.
The bloc denoted 'service PC can also transmit such commands.
Figure 2 shows a drawing in perspective of a radiographic generator, as it can
be used in practice for radiographic exposures in a hospital. This generator
comprises the following elements, that are shown in connection with the
reference signs set forth below :
1 : cathode;
2 : rotating anode;
3 : stator;
4 : rotor;
5 : tube of the radiographic illumination source;
6 : glass casing;
7 : filters;
8 : collimators;
9 : radiographic illumination bundle.
Definitions
Hereinafter are set forth - for a better understanding of the present invention
- the definitions of a few terms used in the description that follows, as well as
in some of the claims.
Also are mentioned the order of magnitude of some of the time periods or
intervals that are mentioned in such definitions.
• Integration time : this is the time during which the digital
radiographic panel, or Flat Panel Detector, is 'open', this means
integrates the signals. This time amounts to approximately 550 msec,
so about half a second, up to 3 sec at maximum.
Exposure time : this is the time during which the radiographic
generator effectively transmits radiographic illumination to the
patient; this time in practice is more or less in the same order of
magnitude as the integration time; this is a feature of the generator
settings; this should be shorter than the integration time under
practical circumstances, otherwise information is lost.
Prep-delay or generator delay-time : this is the time that runs from the
receipt by the generator of a prep-signal, and the time that the rotating
anode is up to speed, and/or the time that the filament wire or
incandescent wire is up to temperature (red/white). This is dependant
upon the type of generator and is in the order of magnitude of 0.5 up
to 3 sec.
Panel delay time : a distinction should be made between the panel
delay time and the generator delay time. The panel delay time is
equal to the so-called reset time. This is the time that the radiographic
detector needs before it can detect radiographic signals. This time is in
the order of magnitude of 100 to 200 milliseconds. This still is
something else than the panel wake-up time : this time amounts to
approx. 2 seconds. Not all panels are characterised by a wake-up time.
There exist Flat Panel Detectors that are always in wake-up state. The
total panel delay time thus is the sum of the above two values, so
amounts to approx. 2.1 up to 2.2 sec.
Radiographic digital detector : this is a radiographic detector for the
direct digital detection of radiographic images on a storage medium.
Examples of such detectors are described in the Handbook of Medical
Imaging, previously cited.
An essential item is the determination of the prep delay time of the
radiographic generator.
When the prep-button is activated, the prep-signal is submitted to the
radiographic generator, implying that the rotating anode is brought up to
speed, and the filament or incandescent wire is heated (this takes a delay time
1).
Also at the time of the submission of the prep signal, the DR panel is
activated (if necessary). The patient waits and stops breathing for a while (in
case of a chest exposure).
After the expiration of this delay the exposure or effective illumination can
start.
When the expose button is activated, a signal is sent from the retrofit box to
the panel, to start the reset. When this has taken place, over the retrofit box a
signal is sent to the generator to apply the high voltage or tension over the
cathode/anode system. When this has effectively taken place (implying a
delay 2), the actual exposure can start, and thus also the integration of the DR
panel. When this stops, the DR panel is read-out.
All of the above preferably is implemented by hardware links although
wireless communications between the different elements of a radiographic
system can also be used.
The goal of the invention now is to determine the delay 1, this is the time the
generator needs to be up to speed, more in particular to bring the rotating
anode to its usual operational speed, and to heat the filament wire to its usual
operational temperature.
This is a stage that takes place before the actual radiographic exposure, a
preparatory stage.
In practice, any radiographic generator yields a signal either visually or
orally, to indicate that the actual radiographic exposure starts. This can take
the form of a ding-dong, a light that starts to shine or blink, an icon on a
display, or a combination of any of the above means.
The generator is put in a so-called 'free exposure state', this means without
being coupled to a digital radiographic detector. To this end, use can be
made of a film, or stimulable phosphor screen (Computed Radiography, CR),
or simply no image storage medium.
Suppose that the prep delay time of the apparatus is set at exactly 10 seconds.
This means that in the retrofit box a delay time is set of 10 seconds,
differently phrased, after the expiration of 10 seconds as from the activation
of the prep and expose button, the expose signal is triggered.
A signal is than sent from the retrofit box to the generator to start the
exposure. But if the generator after ten seconds is not fully up to speed
and/or the filament wire is insufficiently heated, no exposure takes place.
This time can be set in various instalments, starting from a sufficiently high
value, and gradually descending.
For the purpose of the present invention, a sufficiently high delay time
should be understood as being a time value whereby the radiographic
generator has brought its rotating anode fully up to operational speed, and
whereby the filament wire is sufficiently heated for use in practice. For the
majority of radiographic generators 10 seconds is sufficient for the above
purposes; if need be one can start by setting the first value at 15 seconds for
the delay-time.
At a given set time, one will note that the signal of the exposure of the
generator will be notified; this is than the prep-delay time or start-up time for
the given radiographic generator.
This time is determined by means of a binary method. After three to four
attempts at various pre-determined time delays, one knows the prep delay
time of the specific radiographic generator that is at hand.
Thereafter the retrofit box can be placed in the usual operational mode. The
delay time of the radiographic generator is then known to the retrofit box.
How will then the sequence take place for a radiographic exposure with a
retrofit box, for which the prep delay time of the operationally linked
generator is known, and which is placed in its usual operational mode ?
We start from the working assumption that the radiographic operator has
activated the prep and exposure buttons simultaneously.
In practice this is not always the case. In case the operator activates first the
prep button, causing the retrofit box to transmit the preparation signal to the
radiographic generator, and the operator waits sufficiently long before
activating the exposure button, the problem as set forth supra, does not arise.
In such a case, the radiographic generator will be ready (this means its anode
will be fully operational and the filament wire sufficiently heated, at the
moment the operator activates the expose button, and whereby the retrofit
box transmits the corresponding exposure signal to the radiographic
generator).
When the operator then pushes through, the prep signal is directly
transmitted to the generator. The generator is then brought to speed, and has
sufficient time for this action.
After expiration of the prep delay time, the retrofit box sends an exposure
request signal to the DR panel. This will trigger the reset operation, which
takes approximately 100 milliseconds. Thereafter the DR. panel is ready to
capture the image.
Thereafter the integration starts automatically. This triggers the expose
signal OK, and over the retrofit box a signal is sent to the generator that it
can start the exposure. The radiographic generator then effectively starts the
radiographic exposure, whereupon the DR panel will capture and integrate
the radiographic image.
So, in short : according to the method of our invention it is determined by a
series of decreasing chosen values for the delay time whether a signal for the
confirmation of the start of the radiographic exposure is rendered by the
radiographic generator. The last value of the chosen delay time whereby still
such a confirmation signal is rendered, is retained as standard operational
value for the delay time of the radiographic system,
More complex methods can be envisaged to determine the prep delay time.
Such methods can be based on the signal to noise image parameters, on a
shifting of the integration time, but these are unnecessarily complicated. The
above described method is characterised by its simplicity, and consequently
by its robustness in practical circumstances.
What follows hereinafter is a description of a practical embodiment of the
method of the invention, applied in a real-life situation.
Example
In a concrete example the method for the determination of the prep delay
time comprised the following steps.
This method was applied using the following apparatus :
• The radiographic generator used was a GENIT 80 W apparatus,
supplied by Siemens AG, Germany;
• The radiographic tube used was an apparatus 'X-ray Tube Housing
Assembly S 150/40/80 C - 100 L', available from Dunlee;
• The generator console used was a Touch Desk (104 10 669) available
from Siemens AG, Germany.
The generator was set in the 'free exposure state', simply by not using any
image storage medium in the example according to the invention.
The retrofit box is connected to the radiographic generator.
For the setting of the exposure parameters of the generator, use is being
made of a two-point exposure : the exposure setting (the level of the high
voltage applied) was set at 70 kV, and the exposure dose was set at 5 mAs.
At each of the following steps, the prep/expose button on the retrofit box was
activated at full, this means prep and expose button were activated
simultaneously.
In an initial step, the generator delay time is set at 10 sec. This means that
after exposure of 10 sec, as from the transmittal of the prep signal from the
retrofit box to the generator, the expose signal is equally sent from the
retrofit box to the generator.
In this case, the generator yielded immediately an oral confirmation signal
(by means of a buzzer), indicating that the exposure could effectively start
after this period of 10 sec had expired.
This means that the generator delay time is effectively inferior to the set time
of 10 sec. In a subsequent step, the generator delay time was set at a lower
value, in this concrete case, at half the original value, so at 5 sec.
Again the button on the retrofit box is fully pressed, so prep and exposure
button are both activated.
We noted that after expiration of this time period of 5 seconds, again as from
the transmittal of the prep signal to the generator, the expose signal is
transmitted to the generator, and promptly hereupon the oral confirmation
signal is given by the generator.
So the actual exposure started after expiration of these 5 seconds, indicating
that the generator delay time was effectively shorter that the set time of 5
seconds.
Hereupon, in a next step, the generator delay time was set again at half the
previous value, so at 2.5 sec.
Also in this case, promptly after the expiration of this delay time of 2.5 sec, a
positive confirmation signal was noted. The effective generator delay time
consequently was shorter than 2.5 sec.
Hereupon in a next step, the generator delay time was set at 1 second. In this
case we did not note a positive confirmation signal after expiration of this
time period of 1 second.
This means that the effective generator delay time is superior to 1 second.
As a result, is a next step the generator delay time was set at 1.5 sec. In this
case again, after expiration of this period of 1.5 seconds, a positive
confirmation signal was noted.
The conclusion from the above series of events is that the effective generator
delay time is situated between 1 and 1.5 seconds. As a result the delay
time was set at 1.5 seconds, and this value was used as standard operational
value for the delay time of the radiographic system in further use.
By applying the above manner and method, it is assured that after expiration
of this standard operational value, the generator effectively is apt to start the
radiographic exposure.
After determination of the generator delay time by applying the above
method, this time period was set as standard operational value in a retrofit
box, and an exposure was performed by means of a radiographic digital
detector marketed under the brand name PaxScan 4343 , available from
Varian Medical Systems, Salt Lake City, Utah, USA.
The problems cited at the introduction of this specification did not occur.
The radiographic imaging method when using such a digital flat panel
detector in a usual operational mode is then as follows :
The prep/expose button on the retrofit box is fully pressed, whereupon a prep
signal is transmitted to the generator. The generator will then bring the
rotating anode at full operational speed, and takes care that the filament wire
is fully heated. After expiration of the standard operational generator delay
time of 1.5 seconds, a signal is sent from the retrofit box to the flat panel
detector, a so-called exposure request signal. Hereupon a reset of the digital
detector takes place. After expiration of this reset signal (in the order of
magnitude of 100 microseconds) the digital detector is ready to detect the
radiographic signal. Hereupon a signal is sent to the generator indicating the
radiographic exposure can effectively start. Meanwhile the digital detector
remains in the 'open' mode to capture the radiographic illumination. Since
the generator delay time has effectively expired, the exposure starts, and the
capture, resp. storage of the radiographic illumination signal by the digital
detector takes place. A typical illumination time and corresponding
integration time of the digital detector amounts to approx. 550 milliseconds.
In practical circumstances, use is often made of a three-point exposure,
whereby an AEC (Automatic Exposure Control) module is used.
This is a method for controlling the radiographic illumination dose, known to
the person skilled in the art.
Claims
1. Method for the determination of the delay time of a radiographic generator
used in medical radiographic systems, and the use hereof as standard
operational value for the delay time of the corresponding radiographic
system, comprising the following steps :
• Selection of a sufficiently high delay-time for the radiographic
generator on a retrofit box;
• Simultaneous transmission of the preparation- and exposure signal
from the retrofit box to the generator console;
• Determining whether at the expiration of the selected delay time a
confirmation signal for the start of the radiographic exposure has been
submitted by the radiographic generator;
• In case such a confirmation signal has been submitted, repeating the
abovementioned three steps, whereby the delay-time is reduced by a
factor two;
• In case no such confirmation signal has been submitted, repeating
once the abovementioned three steps, whereby a value is selected for
the delay time mid-way the value whereby a confirmation signal still
has been obtained, and the value whereby such signal has not been
obtained any more;
• The last value of the selected delay-time whereby a confirmation
signal still has been given by the radiographic generator, is retained as
standard operational value for the delay time of the radiographic
system by the retrofit box.
2. Method according to claim 1, wherein the initially selected sufficiently
high delay time amounts to at least 10 seconds.
3. Method according to claim 1 or 2, wherein the preparation and exposure
signals are transmitted simultaneously by simultaneous activation of the
preparation and exposure buttons on a retrofit box.
4. Method for taking a radiographic exposure, whereby the radiographic
image is captured by a radiographic digital detector and, in case the
radiographic operator generates an exposure signal to the retrofit box at a
time that the delay time of the generator, counted as from the submission of
the preparation signal by the operator, has not expired yet, that the retrofit
box transmits this exposure signal to the radiographic generator after
expiration of the standard operational delay time as determined by the
method set forth in any of the claims 1 through 3, and counted as from the
transmission of the preparation signal from the retrofit box to the
radiographic generator.
5. Method according to claim 4, wherein the retrofit box transmits the
exposure signal to the radiographic generator, after a positive reset signal has
been received from the digital radiographic detector.
6. Radiographic recording system, comprising a radiographic generator, a
console and an exposure unit, a digital radiographic detector, a retrofit box
and means for detecting by the retrofit box of a preparation signal and an
exposure signal, characterised in that the retrofit box uses a standard
operational value for the delay time for the transmission of the exposure
signal to the generator, whereby said standard operational value is
determined by means of the method set forth in any of claims 1 through 3.
7. Radiographic recording system according to claim 6, wherein the means
for detecting the preparation signal and the exposure signal comprise a twostage
push button operationally coupled to the retrofit box.